JPS5932136B2 - Brain pressure measuring device - Google Patents
Brain pressure measuring deviceInfo
- Publication number
- JPS5932136B2 JPS5932136B2 JP51102399A JP10239976A JPS5932136B2 JP S5932136 B2 JPS5932136 B2 JP S5932136B2 JP 51102399 A JP51102399 A JP 51102399A JP 10239976 A JP10239976 A JP 10239976A JP S5932136 B2 JPS5932136 B2 JP S5932136B2
- Authority
- JP
- Japan
- Prior art keywords
- pressure
- detection bag
- brain
- measuring device
- liquid
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/03—Detecting, measuring or recording fluid pressure within the body other than blood pressure, e.g. cerebral pressure; Measuring pressure in body tissues or organs
- A61B5/031—Intracranial pressure
Description
【発明の詳細な説明】
本発明は、手術後等の脳圧の測定を行うための装置に関
するものである。DETAILED DESCRIPTION OF THE INVENTION The present invention relates to an apparatus for measuring cerebral pressure after surgery or the like.
脳圧、即ち脳硬膜内における脳及び髄液の圧力を、頭蓋
骨、頭皮等に作られた穴を通して、体外に誘導、測定、
記録する方法として、従来空気圧平衡法、電気的周波数
変換法がある。Brain pressure, that is, the pressure of the brain and cerebrospinal fluid within the dura mater, is guided and measured outside the body through a hole made in the skull, scalp, etc.
Conventional recording methods include the pneumatic balance method and the electrical frequency conversion method.
前者は空気圧の供給が必要なため装置が大きくなり、し
かも高価である等の欠点があり、後者は取出しの不便、
高価である等の欠点がある。The former requires a supply of air pressure, making the device large and expensive, and the latter has drawbacks such as inconvenience and inconvenience in taking out the device.
It has drawbacks such as being expensive.
また両者はともに患者が寝返ることにより脳圧指示値が
大きく変動するという重大な欠点がある。In addition, both methods have a serious drawback in that the indicated cerebral pressure value fluctuates greatly when the patient turns over.
本発明はこのような諸問題を解決しようとするもので検
出端として、液体を封じ込めた定容積の検出袋を用いて
、脳圧を流体圧に変え、これを圧力計で測るようにした
ことを特徴とするものである。The present invention aims to solve these problems by using a fixed-volume detection bag containing liquid as a detection end to convert brain pressure into fluid pressure, which is then measured with a pressure gauge. It is characterized by:
これにより短い応答時間でしかも十分な精度が得られる
と共に、患者の寝返りによっても圧力指示値が変化せず
、製造簡易、堅牢、廉価、取扱い簡単である等の効果を
上げることができる。As a result, sufficient accuracy can be obtained with a short response time, and the pressure indication value does not change even when the patient turns over, making it easy to manufacture, robust, inexpensive, and easy to handle.
以下図面を参照して説明すると、第１図において１は頭
皮、２は頭蓋で、一部が手術の時に切り外され、再び元
の状態に収められたものである。The following will be explained with reference to the drawings. In FIG. 1, 1 is the scalp, and 2 is the cranium, a portion of which was removed during surgery and returned to its original state.
このように、切り外された時に頭蓋の一部に孔３があけ
られ、頭蓋の内側に検出袋４をおき、検出袋の導入管部
４ａを孔３を通して外部に出し、そのような状態で頭蓋
を元の位置に嵌める。In this way, when the skull is cut out, a hole 3 is made in a part of the skull, a detection bag 4 is placed inside the skull, and the introduction tube part 4a of the detection bag is brought out through the hole 3. Put the skull back into place.
このようにすることにより硬膜５と頭蓋２との間に検出
袋４が収められる。By doing so, the detection bag 4 is housed between the dura mater 5 and the skull 2.
検出袋としては考えられる脳圧の範囲では余り伸び縮み
せず、かつ十分柔らかい材質、例えばポリエチレンで、
平坦な円形で直径２〜５ＣｒｒＬ、導入管部４ａの直径
が１〜５ｍｍ程度に作られる。The detection bag should be made of a material that does not expand or contract much within the range of brain pressure that can be considered and is sufficiently soft, such as polyethylene.
It is made into a flat circular shape with a diameter of 2 to 5 CrrL, and the diameter of the introduction pipe portion 4a is about 1 to 5 mm.
そうすることにより、不要になった時に患部を切開する
ことなく検出袋を容易に引き出せる。By doing so, the detection bag can be easily pulled out without incising the affected area when it is no longer needed.
このような検出袋に液体供給源６より弁７を介して液を
注入して、検出袋の内容積を変えるとき、その容積と検
出袋内の流体の圧力Ｐｏの関係は第２図のようになる。When the internal volume of the detection bag is changed by injecting liquid into such a detection bag from the liquid supply source 6 through the valve 7, the relationship between the volume and the pressure Po of the fluid in the detection bag is as shown in Fig. 2. become.
即ち、この特性には、顕著な平坦部、又は勾配が他と比
べて極めて小さい部分Ａが現われ、特に重要なことは、
この平坦部での検出袋内の圧力は十分な精度で脳圧Ｐｉ
と等しいことが判明した。That is, in this characteristic, a remarkable flat part or a part A where the slope is extremely small compared to others appears, and what is particularly important is that
The pressure inside the detection bag at this flat area is determined to be the brain pressure Pi with sufficient accuracy.
was found to be equal to
これは、検出袋の容積を変えることにより、その形状が
変化し、検出袋と脳の硬膜との接する面が、特性の平坦
部では、脳圧を検出袋内の流体に伝達するのに望ましい
状態となるためである。This is because by changing the volume of the detection bag, its shape changes, and when the contact surface between the detection bag and the dura mater of the brain has a characteristic flat area, it is difficult to transmit cerebral pressure to the fluid inside the detection bag. This is to achieve a desirable state.
実際、この接面が平面（又は接面の平均的な曲率が０）
であれば、硬膜および検出袋の張力が、圧力Ｐ１とＰＯ
に差を生じさせる原因とはならないことが理論的に云え
る。In fact, this tangent surface is a plane (or the average curvature of the tangent surface is 0)
If the tension in the dura mater and detection bag is equal to the pressure P1 and PO
Theoretically, it can be said that this is not the cause of the difference.
従って平坦部Ａに達した時を検出し、それと同時に弁７
を閉じ液の注入を停止し検出袋及びこれから圧力計に至
る管路内には、液体が封じこまれ、その体積は一定に保
たれる。Therefore, it is possible to detect when the flat part A is reached, and at the same time, the valve 7
When the sensor is closed, the injection of liquid is stopped, and the liquid is sealed in the detection bag and the pipeline leading from it to the pressure gauge, and its volume is kept constant.
このため、以後検出袋と硬膜との平面的接触が保たれ、
この液体の圧力を圧力計８で測定することにより脳圧を
連続的に測定することができる。Therefore, from now on, planar contact between the detection bag and the dura mater is maintained.
By measuring the pressure of this liquid with the pressure gauge 8, brain pressure can be continuously measured.
なお、検出袋としてゴムのような材料を用いると、脳圧
によりゴム袋が伸び縮みして上記の接触状態が一定には
保たれないので不可である。Note that it is not possible to use a material such as rubber as the detection bag because the rubber bag expands and contracts due to brain pressure and the above-mentioned contact state cannot be maintained constant.
又圧力で容積が変わるような圧力計も望ましくない。Also, a pressure gauge whose volume changes depending on the pressure is not desirable.
上記の実施例では、検出袋の中に液体を供給するように
しているが、予め検出袋の中に液体を充満させたものを
頭蓋内に挿入し、液体を徐々に抜いて行く過程で、平坦
部Ａを検出するようにしてもよい。In the above embodiment, liquid is supplied into the detection bag, but in the process of inserting the detection bag filled with liquid into the skull and gradually draining the liquid, The flat portion A may also be detected.
次に脳圧を自動的に測定できる実施例について説明する
。Next, an embodiment that can automatically measure cerebral pressure will be described.
第３図の曲線ａは第２図の曲線と同じ検出袋内圧力を示
すものであるが、この圧力信号を、むだ時間又はおくれ
要素により遅らせることにより曲線すを得る。Curve a in FIG. 3 shows the same detected pressure inside the bag as the curve in FIG. 2, but the curve a is obtained by delaying this pressure signal by a dead time or lag element.
この両曲線の平坦部Ａ 、 Ａ’では両曲線が他の部分
よりも接近するので、両曲線における圧力差が小さい。At the flat parts A and A' of these two curves, the two curves are closer to each other than at other parts, so the pressure difference between the two curves is small.
従ってその圧力差が適当に設定した微小値ΔＰよりも小
さくなった時点を検出することにより、これを脳圧測定
の開始点に設定することができる。Therefore, by detecting the point in time when the pressure difference becomes smaller than an appropriately set minute value ΔP, this can be set as the starting point for cerebral pressure measurement.
第４図は、その設定点検出装置のブ七ツクダイヤグラム
で、検出袋４内に液体供給源より液体を電磁弁９を介し
て注入するようにし、その圧力を圧力変換器１０により
電気信号に変える。FIG. 4 is a block diagram of the set point detection device, in which liquid is injected into the detection bag 4 from a liquid supply source through a solenoid valve 9, and the pressure is converted into an electrical signal by a pressure transducer 10. change.
その電気信号は直接比較回路１１に送られる回路と遅延
回路１２を通る回路とに分けられ、それにより、前記の
曲線ａ、ｂに相当する信号が得られる。The electrical signal is divided into a circuit that is directly sent to the comparison circuit 11 and a circuit that passes through the delay circuit 12, whereby signals corresponding to the curves a and b described above are obtained.
これを比較回路１１で比較し、両信号の差が設定された
微小値ΔＰに達した時信号を発生し、その信号は増巾器
１３で増巾されて電磁弁９に送られ、弁を閉じる。The comparator circuit 11 compares these signals, and when the difference between the two signals reaches a set minimum value ΔP, a signal is generated.The signal is amplified by the amplifier 13 and sent to the solenoid valve 9, which controls the valve. close.
かくて脳圧を高精度で管路内の流体圧に変換することが
でき、以后この圧力を測定することにより脳圧を連続的
に測定することができる。In this way, brain pressure can be converted into fluid pressure within the conduit with high accuracy, and by subsequently measuring this pressure, brain pressure can be continuously measured.
脳圧は脳内の各部で異なる。Brain pressure differs in each part of the brain.
即ち第５図で、上部の圧力をＰｌ、下部の圧力をＰ２と
すれば、Ｐ２＝Ｐ１＋ρ（ｉｉＩｈ。That is, in FIG. 5, if the pressure at the top is Pl and the pressure at the bottom is P2, then P2=P1+ρ(iiih).
で、ρは脳の平均密度、ｇは重力の加速度である。where ρ is the average density of the brain and g is the acceleration of gravity.
前述のように従来の方法では、患者の寝返りにより、ρ
ｇｈ１に相当する値（約１００ｍｍ水柱）の変動が指示
値に現われる。As mentioned above, in the conventional method, due to the patient turning over, ρ
Fluctuations in the value corresponding to gh1 (approximately 100 mm water column) appear in the indicated value.
因みに脳圧の正常値は約１５０ｍｍ水柱である。Incidentally, the normal value of cerebral pressure is approximately 150 mm of water column.
しかるに本発明では、第５図の圧力計の指示値は、管路
内の液体密度をρ′とすれば、脳圧Ｐ、。However, in the present invention, the indicated value of the pressure gauge in FIG. 5 is the intracranial pressure P, where ρ' is the liquid density in the conduit.
Ｐ２に対してそれぞれ
Ｐ＝Ｐ１−ρ′ｇｈ２
Ｐ ’＝ Ｐ２−ρ′ｇ（ｈ１＋ｈ２）
となるが、後者に曲成のＰ２を代入することにより、液
体の密度ρ′が脳の平均密度ρに等しいρ′−ρである
ような液体例えば生理的食塩水を用いれば、関係
Ｐ＝Ｐ’
が得られ、寝返りの影響を受けない脳圧指示値が得られ
る。For P2, P = P1 - ρ'gh2 P' = P2 - ρ'g (h1 + h2), but by substituting the curved P2 into the latter, the density ρ' of the fluid becomes the average density ρ of the brain. By using a liquid, such as physiological saline, in which ρ' - ρ is equal to , the relationship P=P' can be obtained, and a cerebral pressure indication value that is not affected by turning over can be obtained.
従って本発明は患者の姿勢に影響を受けない大きな特徴
を有する。Therefore, the present invention has the great feature of not being affected by the patient's posture.
第１図は本発明の一実施例を示す概略図、第２図及び第
３図は検出袋の内容積と検出袋内の圧力の関係を示す図
、第４図は本発明の他の実施例を示す図、第５図は寝返
りによる脳圧指示値の不変性を説明する図である。
１・・・・・・頭皮、２・・・・・・頭蓋、３・・・・
・・孔、４・・・・・・検出袋、４ａ・・・・・・導入
管部、５・・・・・・硬膜、６・・・・・・液体供給源
、７・・・・・・弁、８・・・・・・圧力計、９・・・
・・・電磁弁、１０・・・・・・圧力変換器、１１・・
・・・・比較回路、１２・・・・・・遅延回路、１３・
・・・・・増巾器。FIG. 1 is a schematic diagram showing one embodiment of the present invention, FIGS. 2 and 3 are diagrams showing the relationship between the internal volume of the detection bag and the pressure inside the detection bag, and FIG. 4 is a diagram showing another embodiment of the present invention. A diagram showing an example, FIG. 5, is a diagram illustrating the invariance of the cerebral pressure indication value due to turning over. 1...Scalp, 2...Cranium, 3...
... Hole, 4 ... Detection bag, 4a ... Introductory pipe section, 5 ... Dura mater, 6 ... Liquid supply source, 7 ... ...Valve, 8...Pressure gauge, 9...
...Solenoid valve, 10...Pressure transducer, 11...
... Comparison circuit, 12 ... Delay circuit, 13.
......Amplifier.
Claims (1)
て注入する液体供給手段と、該検出袋内の圧力を測定す
る装置とを有し、前記液体供給手段と測定装置と前記検
出袋とを連通ずる可撓性の導管とよりなり、前記圧力測
定装置は、導管および検出袋の系の測定状態における内
容積に対する内液圧の特性曲線の平坦部のほぼ中央を検
出できる測定圧力範囲を含み、前記系内に脳の平均密度
とほぼ等しい密度を有する液体が前記平坦部のほぼ中央
に対応する量だけ封入されていることを特徴とする脳圧
測定装置。1 It has a non-stretchable detection bag, a liquid supply means for injecting liquid into the detection bag through a valve, and a device for measuring the pressure inside the detection bag, and the liquid supply means and the measuring device The pressure measuring device is comprised of a flexible conduit communicating with the detection bag, and the pressure measuring device is capable of detecting approximately the center of a flat portion of a characteristic curve of internal fluid pressure with respect to internal volume in a measurement state of the system of the conduit and detection bag. A brain pressure measurement device, characterized in that a liquid that includes a measurement pressure range and has a density approximately equal to the average density of the brain is sealed in the system in an amount corresponding to approximately the center of the flat portion.
Priority Applications (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP51102399A JPS5932136B2 (en) | 1976-08-27 | 1976-08-27 | Brain pressure measuring device |
| US05/827,740 US4147161A (en) | 1976-08-27 | 1977-08-25 | Intracranial pressure monitoring method and system |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP51102399A JPS5932136B2 (en) | 1976-08-27 | 1976-08-27 | Brain pressure measuring device |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPS5348387A JPS5348387A (en) | 1978-05-01 |
| JPS5932136B2 true JPS5932136B2 (en) | 1984-08-07 |
Family
ID=14326360
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP51102399A Expired JPS5932136B2 (en) | 1976-08-27 | 1976-08-27 | Brain pressure measuring device |
Country Status (2)
| Country | Link |
|---|---|
| US (1) | US4147161A (en) |
| JP (1) | JPS5932136B2 (en) |
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| EP3838131A3 (en) | 2014-04-17 | 2021-12-15 | Branchpoint Technologies, Inc. | Wireless intracranial monitoring system |
Citations (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS515886A (en) * | 1974-07-02 | 1976-01-19 | Takiguchi Hiroyuki | SEITAINAIATSUSOKUTE ISOCHI |
Family Cites Families (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US327403A (en) * | 1885-09-29 | Pateiok eneas mcdonnell | ||
| US3598106A (en) * | 1970-03-20 | 1971-08-10 | Eric Buning | Intravaginal therapeutic muscle exerciser and method of use |
| US3789667A (en) * | 1972-02-14 | 1974-02-05 | Ladd Res Ind Inc | Fiber optic pressure detector |
| US3958562A (en) * | 1974-05-30 | 1976-05-25 | Hakim Company Limited | Implantable pressure sensor |
| US4006735A (en) * | 1974-07-16 | 1977-02-08 | Hittman Corporation | Pressure sensor apparatus |
-
1976
- 1976-08-27 JP JP51102399A patent/JPS5932136B2/en not_active Expired
-
1977
- 1977-08-25 US US05/827,740 patent/US4147161A/en not_active Expired - Lifetime
Patent Citations (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS515886A (en) * | 1974-07-02 | 1976-01-19 | Takiguchi Hiroyuki | SEITAINAIATSUSOKUTE ISOCHI |
Also Published As
| Publication number | Publication date |
|---|---|
| JPS5348387A (en) | 1978-05-01 |
| US4147161A (en) | 1979-04-03 |
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